Insoluble gas-filled microspheres containing a hydrophobic barrier

ABSTRACT

The present invention relates to a process for making insoluble gas-filled, pressure-resistant microspheres containing a liquid or solid hydrophobic barrier within the microsphere shell, and products of this process. This barrier serves to decrease the rate of gas exchange between the microsphere and the aqueous environment surrounding the microsphere and thus enhances resistance to pressure due to gas exchange.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation application of U.S. Ser. No.08/972,152 filed Nov. 17, 1997, now U.S. Pat. No. 5,965,109, which is afile wrapper continuation application of U.S. Ser. No. 08/660,480 filedJun. 7, 1996, which is a continuation-in-part application of U.S. Ser.No. 08/477,510 filed Jun. 7, 1995, now U.S. Pat. No. 5,730,955, which isa continuation-in-part application of U.S. Ser. No. 08/284,782 filedAug. 2, 1994, now U.S. Pat. No. 5,562,893.

DESCRIPTION

1. Technical Field

This invention is in the field of ultrasonic imaging. More particularlyit relates to a process for increasing the hydrophobicity ofmicrospheres useful for ultrasonic imaging. The microspheres comprisingmicrobubbles of insoluble gas encapsulated by shells composed of abiocompatible, amphiphilic material contain a liquid or solidhydrophobic barrier formed on the inner surface of the microsphereshell. This barrier serves to decrease the rate of gas exchange betweenthe microsphere and the aqueous environment surrounding the microsphereand thus enhances resistance to pressure instability due to gasexchange.

2. Background

Diagnostic ultrasonic imaging is based on the principle that waves ofsound energy can be focused upon an area of interest and reflected insuch a way as to produce an image thereof. The ultrasonic transducer isplaced on a body surface overlying the area to be imaged, and ultrasonicenergy in the form of sound waves is directed toward that area. Asultrasonic energy travels through the body, the velocity of the energyand acoustic properties of the body tissue and substances encountered bythe energy determine the degree of absorption, scattering, transmissionand reflection of the ultrasonic energy. The transducer then detects theamount and characteristics of the reflected ultrasonic energy andtranslates the data into images.

As ultrasound waves move through one substance to another there is somedegree of reflection at the interface. The degree of reflection isrelated to the acoustic properties of the substances defining theinterface. If these acoustic properties differ, such as withliquid-solid, liquid-liquid or liquid-gas interfaces, the degree ofreflection is enhanced. For this reason, gas-containing contrast agentsare particularly efficient at reflecting ultrasound waves. Thus, suchcontrast agents intensify the degree of reflectivity of substancesencountered and enhance the definition of ultrasonic images.

Ophir and Parker describe two types of gas-containing imaging agents:(1) free gas bubbles; and (2) encapsulated gas bubbles (Ultrasound inMedicine and Biology 15(4):319-333 (1989)), the latter having beendeveloped in an attempt to overcome instability and toxicity problemsencountered using the former. Encapsulated gas bubbles, hereinafterreferred to as "microspheres," are composed of a microbubble of gassurrounded by a shell of protein or other biocompatible material. Onesuch imaging agent is ALBUNEX® (Molecular Biosystems, Inc., San Diego,Calif.) which consists of a suspension of air-filled albuminmicrospheres.

Generally, microspheres of a particular gas exhibit improved in vivostability when compared to free bubbles of the same gas. However, mostmicrospheres still have relatively short in vivo half lives whichcompromise their usefulness as contrast agents. This instability in vivowas thought to result from the collapse or breakdown of the shells underpressure resulting in rapid diffusion of the gas from the microspheres.Thus, many recent efforts have centered on improvements to the shell asa way of increasing in vivo stability. Known improvements relating toprotein-shelled microspheres include coating the protein shell withsurfactants (Giddy, WO 92/05806) and chemical cross-linking of theprotein shell (Holmes et al., WO 92/17213).

Additional efforts directed toward improving microsphere stabilityinclude the use of non-proteinaceous shell-forming materials. Bichon etal. (European Patent Application 458,745A1) and Schneider et al. (Inv.Radiol. 27:134-139 (1992)) describe the production of polymeric"microballoons" made of interfacially deposited polymers encapsulatingvarious gases such as carbon dioxide, nitrous oxide, methane, freon,helium and other rare gases. Klaveness (WO 92/17212) describes the useof chemically-linked, non-proteinaceous amphiphilic moietiesencapsulating "air, nitrogen, oxygen, hydrogen, nitrous oxide, carbondioxide, helium, argon, sulfur hexafluoride and low molecular weight,optionally fluorinated, hydrocarbons such as methane, acetylene orcarbon tetrafluoride." Erbel et al. (U.S. Pat. No. 5,190,982) describethe use of polyamino-dicarboxylic acid-co-imide derivatives.

More recently, Schneider et al. (U.S. Pat. No. 5,413,774) havedemonstrated that microspheres containing gases with certain physicalproperties have improved stability. It is theorized that microsphereinstability is caused by the increase in pressure to which microspheresare exposed once they are introduced into the circulatory system.Although Schneider et al. do not speculate as to the mechanismresponsible for their observation of enhanced pressure resistance, webelieve it is due to the effects of gas solubility on the rate of gasexchange with the aqueous environment.

According to Henry's law, the solubility of a given gas in solutionincreases as pressure increases. When a bubble of gas in solution issubjected to pressure, the rate of gas exchange between the gas in thebubble and the surrounding solution will increase in proportion to theamount of pressure, and the bubble of gas will eventually becomecompletely solubilized. The more insoluble the gas is in the surroundingsolution, the longer it will take for a bubble to become completelysolubilized.

If the bubble of gas is surrounded by a shell, i.e., in the form of amicrosphere, the effects of gas exchange are still observed, sincemicrosphere shells do not completely eliminate contact between gas inthe microsphere and the surrounding solution. Hence, when microspheressuspended in solution are subjected to pressure, the gas inside themicrospheres eventually becomes solubilized in the surrounding solutionwhich results in collapse of the microspheres.

In order to inhibit the exchange of gas in the microsphere center withthe surrounding aqueous environment, the present invention describes aprocess for increasing the hydrophobicity of the microsphere shell byforming a solid or liquid hydrophobic barrier on the inner surface ofthe microsphere shell. Microspheres formed by this process will exhibitdecreased water permeability and thus enhanced resistance to pressureinstability due to gas exchange.

DISCLOSURE OF THE INVENTION

The present invention provides insoluble gas-filled microspherescontaining a liquid or solid hydrophobic barrier on the inner surface ofthe microsphere shell which increases the overall hydrophobicity of themicrosphere. In particular, the present invention provides for a processof producing microspheres comprising a shell formed from amphiphilic,biocompatible material surrounding a microbubble of at least onebiocompatible insoluble gas and a liquid or solid hydrophobic compoundbarrier formed at the inner surface of the microsphere shell, saidbarrier decreasing the permeability of the shell and the rate of gasexchange with the aqueous environment surrounding the microsphere. Inthe present invention, a biocompatible insoluble gas suitable for usewith the present invention is saturated with a hydrophobic "sealer"compound with a boiling point above room temperature. Upon cooling toroom temperature, the hydrophobic compound will condense on thehydrophobic inner shell surface of the microsphere thereby creating anadditional hydrophobic barrier and increasing the overall hydrophobicityof the microsphere shell. The hydrophobic compound can be inert andincludes, but is not limited to, members of the hydrocarbon, halogenatedhydrocarbon or perfluorocarbon series. The hydrophobic compound can havea linear, branched or cyclic molecular structure.

Hydrophobic compounds within the present invention, when introduced by awater-insoluble gas, can be reactive and capable of covalently bondingto reactive amino acid side chains in the protein of the shell. If someof the reactive material undergoes hydrolysis before it has anopportunity to covalently bond with the proteinaceous shell, theresulting hydrolysis product would also form a hydrophobic deposit onthe inner surface of the microsphere and act as a sealer.

Alternatively, a polymerizable, low-boiling monomer can be introducedwith a water-insoluble gas. Hydrophobic monomers within the presentinvention polymerize inside the microsphere, optionally as a result ofreaction with a chemical initiator or light, to form a polymer layer onthe inner surface of the microsphere. The polymeric material formedincludes, but is not limited to substituted polyethylenes, polystyreneand the like. Preferred polymeric materials include polyacrylate andpolymethacrylate.

In the cases described above, a hydrophobic layer is formed which ischemically and/or physically attached to the inner surface of theproteinaceous shell. In another aspect of the invention, the hydrophobiccompound forms a sponge-like structure within the proteinaceous shelloccupying some or all of the space within the microsphere and containsbiocompatible insoluble gases within the interstices.

The amount of hydrophobic compound introduced in the shell is an amountsufficient to decrease the permeability of the microsphere shell to theaqueous environment. The decrease in permeability of the shell resultsin slower rate of gas exchange with the aqueous environment and isevidenced by enhanced pressure resistance of the microsphere. The amountof hydrophobic compound introduced into the microsphere by the insolublegas can be controlled by its partial vapor pressure. Raising or loweringthe temperature of a bath containing the liquid hydrophobic compoundwill increase or decrease, respectively, the size of the hydrophobiclayer. The partial vapor pressure is dependent on the temperature of thebath containing the hydrophobic compound. For example, insoluble gas canbe saturated with perfluorodecalin (bp. 142° C. at 760 mm Hg) bybubbling the gas through perfluorodecalin that is maintained at 75° C.by standing in a temperature bath. The partial vapor pressure attainedwill be approximately 100 mm Hg. The saturated gas is then mixed with 1%human serum albumin to form microspheres by a cavitation process.

Microspheres formed by ultrasonication generally have a mean diameter of3-5 microns and a shell thickness of approximately 20 nm. While thespecific amount of hydrophobic compound necessary to decrease thepermeability of the microsphere will vary with the hydrophobic compoundand the gas, the gas generally should be saturated with the hydrophobiccompound to give a partial pressure in the range of about 10 to about650 mm Hg, preferably about 50 to about 250 mm Hg.

It is anticipated that with increasing boiling point, the sealercompounds become more efficient and therefore smaller amounts would berequired to obtain the same stabilizing effect. The reason for this isthat higher boiling compounds are adsorbed more strongly to thenaturally hydrophobic inner surface of the microsphere.

Gases suitable for use within the present invention arepharmacologically acceptable and insoluble and include, but are notlimited to, sulfur hexafluoride, perfluoromethane, perfluoroethane,perfluoropropane and perfluorobutane and the like.

Suitable microsphere shell material includes proteins and syntheticamino acid polymers. The material is preferably a protein, and morepreferably human serum albumin.

The microspheres of the present invention may be made by known methodsused to make conventional gas-filled microspheres such as sonication,mechanical cavitation using a milling apparatus, or emulsion techniques.

MODES OF CARRYING OUT THE INVENTION

Microspheres which contain insoluble gases are known to be more pressureresistant than equivalent microspheres containing soluble gases. This isbecause the rate of exchange of the gas with the surrounding aqueousenvironment is slower for an insoluble gas than a soluble gas. However,even insoluble gases eventually escape into the aqueous environmentwhich diminishes the shelf life of insoluble gas-containingmicrospheres.

The present invention relates to the discovery that the stability ofinsoluble gas-containing microspheres can be improved by rendering themicrosphere shells more hydrophobic to diminish the ability of theaqueous environment to come in contact with the microsphere's gas core.This is accomplished by using a process of making microspheres whichincreases the hydrophobicity of microsphere shells by creating a liquidor solid hydrophobic barrier on the inner surface of a microsphereshell. Such a barrier is produced by saturating an insoluble gassuitable for use within the present invention with a hydrophobiccompound, such as a hydrocarbon or perfluorocarbon or the like, at anelevated temperature. Microspheres are then prepared using conventionalcavitation techniques and the hydrophobic compound saturated in the gaswill condense and/or react with the shell material and form a liquid orsolid hydrophobic barrier on the inner surface of the microsphere shell.

Suitable hydrophobic compounds within the present invention include, butare not limited to, hydrocarbons of the general formula, C_(n) H_(2n+2),wherein n=6-12, such as octane (bp=126° C.) or isooctane (bp=99° C.),linear or branched perfluorocarbons of the general formula C_(n)F_(2n+2), wherein n=5-12, such as perfluoropentane (bp=29° C.),perfluorohexane (bp=60° C.), perfluoroheptane (bp=80° C.),perfluorooctane (bp=100° C.) or 1-bromoperfluorooctane (bp=142° C.) andcyclic perfluorocarbons such as perfluoromethylcyclohexane (bp=76° C.),perfluorodecalin (bp=142° C.), and octafluorotoluene (bp 105° C.). Inerthydrophobic compounds within the present invention include, but are notlimited to, perfluorinated alcohols such as 1H,1H-heptafluoro-1-butanol(bp=96° C.), 1H,1H,7H-dodecafluoro-1-heptanol (bp=170° C.), ethers suchas 2,3,4,5,6-pentafluoroanisole and esters such as alkylperfluoroalkanoates.

Reactive hydrophobic compounds include, but are not limited to, activeesters such as linear alkyl trifluoracetates or acyl chlorides with thegeneral formula C_(n) H_(2n+1) COCl, wherein n=4-10, such as hexanoylchloride (bp=152° C.) or C_(n) F_(2n+1) COCl, wherein n=2-10, such asperfluorooctanoyl chloride (bp=132° C.) and cyclic compounds such aspentafluorobenzoyl chloride (bp=159° C.). Acid chlorides of someperfluoro alkanedioic acids, such as tetrafluorosuccinyl chloride,hexafluoroglutaryl chloride and octafluoroadipoyl chloride, which arebifunctional and capable of crosslinking proteinaceous material can alsoserve as hydrophobic compounds. Polymerizable hydrophobic compoundswithin the present invention include, but are not limited to, styrenessuch as pentafluorostyrene (bp=140° C.), alkyl acrylate, CH₂ ═CHCOOR,wherein R=C_(n) H_(2n+1) or C_(n) F_(2n+1), wherein n=1-6 and thecorresponding alkyl methacrylates and fluoroalkyl methacrylates. Alsowithin the present invention are the alkyl-2-cyanoacrylates.

Suitable shell material must be amphiphilic, i.e., containing bothhydrophobic and hydrophilic moieties. It must also be capable of forminga thin layer or skin around the encapsulated gas, which will generallyresult in hydrophilic groups oriented externally and hydrophobic groupsoriented internally. When microspheres are produced to contain insolublegas, this orientation is believed to be enhanced by the presence of theinsoluble gas during microsphere formation.

Protein shells may also optionally incorporate proteins, amino acidpolymers, carbohydrates, lipids, sterols or other substances useful foraltering the rigidity, elasticity, biodegradability and/orbiodistribution characteristics of the shell. The rigidity of the shellcan also be enhanced by cross-linking, for example, with irradiation.

Protein shell material includes both naturally-occurring proteins andsynthetic amino acid polymers which herein are both generally referredto as being in the class of shell materials described as "proteins".Examples of naturally-occurring proteins include gamma-globulin (human),apo-tansferrin human), beta-lactoglobulin, urease, lysozyme, and serumalbumin. Synthetic amino acid polymers can optionally be in the form ofblock or random co-polymers combining both hydrophobic and hydrophilicamino acids in the same or different chains. Moreover, amino acidpolymers can optionally be fluorinated.

The present invention also contemplates the attachment oftarget-specific moieties to the outer shell material of microspheres.Microspheres within the present invention provide a superior deliveryvehicle for such target-specific moieties due to the increased stabilityof the microspheres. Such increased in vivo stability insures deliveryof target-specific moieties to targeted organs or cells via lengthyroutes of administration.

The introduction of the hydrophobic compound in the shell isaccomplished by forming microspheres at elevated temperatures in thepresence of an insoluble gas saturated with a hydrophobic compoundhaving a boiling point above 20° C. For example, perfluoropropane can besaturated with perfluoropentane (bp=30° C.), perfluorohexane (bp=60°C.), perfluoroheptane (bp=80° C.), perfluorooctane (bp=100° C.) orperfluorodecalin (bp=142° C.). The saturated gas is maintained at atemperature above the bath temperature and mixed with 1-5% human serumalbumin to form microspheres by a cavitation technique.

Microspheres containing the hydrocarbon barrier may be made by knownmethods used to make conventional gas-filled microspheres such assonication, mechanical cavitation using a milling apparatus, or emulsiontechniques. Such techniques are exemplified in U.S. Pat. Nos. 4,957,656;5,137,928; 5,190,982; 5,149,543: PCT Application Nos. WO 92/17212; WO92/18164; WO 91/09629; WO 89/06978; WO 92/17213; GB 91/00247; and WO93/02712: and EPA Nos. 458,745 and 534,213 which are incorporated hereinby reference.

Gases suitable for use within the present invention arepharmacologically acceptable, i.e., biocompatible and minimally toxic tohumans and insoluble. The term "insoluble gas" as used herein intendsgases and mixtures of gases which are entirely insoluble, as well asmixtures of gases which contain minor amounts (less than 20% v/v) ofsoluble gas(es) such as air. Insoluble gases are necessary to achieve adesired slow rate of gas exchange with the aqueous environment. The term"biocompatible" means the ability of the gas to be exhaled ormetabolized without the formation of toxic by-products. The term "gas"refers to any compound which is a gas or capable of forming gas at thetemperature at which imaging is being performed (typically normalphysiological temperature) or upon application of ultrasound energy. Thegas may be composed of a single compound or a mixture of compounds. Thegas is preferably a perfluorocarbon which is insoluble in water, whichintends a solubility of less than 0.01 mL of gas per mL of water atatmospheric pressure and a temperature of 25° C. Examples ofperfluorocarbon gases suitable for use within the present invention areperfluoromethane, perfluoroethane, perfluoropropane, perfluorobutane andperfluoroisobutane. This degree of insolubility results in maximumstability in vitro and persistence in vivo. Solubility can be determinedby any appropriate method. See, for example, Wen-Yang Wen et al. (1979)J. Solubility Chem. 8(3):225-246.

Microspheres made by processes within the present invention areechogenic (i.e., capable of reflecting sound waves) being composed ofmaterial having acoustic properties which are significantly differentfrom those of blood or tissue. The maximum size (mean diameter) of themicrosphere is defined by that size which will pass through thepulmonary capillaries. In the case of humans, that size will typicallybe less than about 10 micrometers. Correspondingly, the minimum size isthat which will provide efficient acoustic scattering at the ultrasonicfrequencies typically used for ultrasonic imaging. (The frequency mayvary with the mode of imaging, e.g., transthoracic, transesophageal, andwill normally be in the range of 2-12 MHz.) The minimum size willtypically be about 0.1 micrometers. The typical mean size of themicrospheres used in the invention method will be about 2 to about 7micrometers. This size will permit their passage through capillaries, ifnecessary, without being filtered out prior to reaching the area to beimaged (e.g., where a peripheral venous injection site is used). Thus,microspheres within the present invention will be capable of perfusingtissue and producing an enhanced image of the tissue, organs and anydifferentiation between well-perfused and poorly-perfused tissue,without being injected into the arteries or directly into the area to beimaged. Accordingly, they may be injected into a peripheral vein orother predetermined area of the body, resulting in considerably lessinvasion than the arterial injections required for an angiogram.

The microsphere suspensions may be stored in sterile glass vials aftermanufacturing, or they may be stored in syringes, which are ready foruse in administering the microsphere suspensions.

Microspheres made by processes within the present invention may be usedfor imaging a wide variety of areas. These areas include, but are notlimited to, myocardial tissue, liver, spleen, kidney, and other tissuesand organs presently imaged by ultrasonic techniques. Use ofmicrospheres within the present invention may result in an enhancementof such currently obtainable images.

In terms of method of operation, the use of the subject microsphereswould be the same as that of conventional ultrasonic contrast agents.The amount of microspheres used would be dependent on a number offactors including the choice of liquid carriers (water, sugar solution,etc.), degree of opacity desired, areas of the body to be imaged, siteof injection and number of injections. In all instances, however,sufficient microspheres would be used in the liquid carrier to achieveenhancement of discernible images by the use of ultrasonic scanning.

For use in conventional or harmonic ultrasound imaging, the suspensionof microspheres is injected into a peripheral vein, either as a bolus orcontinuously infused over a period of time, such as one to ten minutes,at about 0.05 to 0.5 cc per kg body weight. Ultrasonic energy is appliedeither continuously or intermittently (i.e., pulsed) to the tissue/organto be imaged, and reflected energy is collected and translated into animage using conventional, commercially available ultrasound imagingequipment.

Two dimensional (2-D) or multidimensional (e.g. three-dimensional (3-D))echocardiography equipment and procedures may be used to acquire theimage. Such procedures and equipment are conventional. Three techniquesused to acquire 3-D images are as follows: In the first, a standardtransducer is used to collect tomographic images. The transducer ismounted on a track and collects images as it moves along the track. Thespeed of motion along the track is defined, so that the spacing betweentomographic images is known. The collection of slices are then meldedtogether to obtain a 3-D image. In the second, a standard transducer isalso used to collect tomographic images. Attached to the transducer is asensor that is able to report the spatial position of the transducer, sothat the relative orientation of various images are known and the imagescan be melded together to generate a 3-D image. In the third, thetransducer consists of a two dimensional array of elements. A onedimensional array of elements is able to acquire a tomographic image;the added dimension allows scanning in the third dimension.

The invention is further illustrated by the following examples. Theseexamples are not intended to limit the invention in any manner. Thedisclosures of the publications, patents, patent applications, andpublished patent specifications referenced in this application arehereby incorporated by reference into the present disclosure.

EXAMPLE 1 Method of Making Microspheres by Mechanical Cavitation

(A) Saturation of Gas

The insoluble gas is saturated with the hydrophobic compound by bubblingit via a fritted gas dispersion tube through the hydrophobic compoundwhich is maintained in a constant temperature bath. The temperature isadjusted to the appropriate level to maintain the required partial vaporpressure. The temperature of the gas line leading to the cavitationchamber must be maintained at or above the bath temperature in order toprevent condensation of the hydrophobic compound from the gas-vapormixture before it reaches the chamber.

(B) Preparation of Microspheres

A 5% human albumin solution (USP) is deaerated under continuous vacuumfor two hours. The vacuum is released by filling the evacuated vesselwith the carrier gas described in (A) above. The solution is adjusted toa temperature (about 68° C.) necessary to achieve local denaturation ofthe albumin upon cavitation via an in line heat exchanger and pumped atabout 100 mL/min into a colloid mill, for example, a 2" colloid mill(Greerco, Hudson N.H., model W250V or AF Gaulin, Everett, Mass., model2F). The gas-vapor mixture is added to the liquid feed just upstream ofthe inlet port at a flow rate of about 120-220 mL/min. The gap betweenthe rotor and the stator is adjusted to about 2/1000th inch and thealbumin solution is milled continuously at about 7000 rpm at a processtemperature of about 73° C.

The dense white solution of microspheres thus formed is immediatelychilled to a temperature of about 10° C. by a heat exchanger, andcollected in glass vials. The vials are immediately sealed.

EXAMPLE 2 Method of Making Microspheres by Sonic Cavitation

Perfluoropropane at a flow rate of 42 mL/minute was saturated withperfluorohexane at 34° C. as described in Example 1 prior to undergoingcontinuous sonication with 1% human serum albumin (flow rate of 80mL/minute) as described by Cerny (U.S. Pat. No. 4,957,656). The densewhite solution of microspheres thus formed was quickly chilled to atemperature of about 10° C. by a heat exchanger and collected in glassvials. The vials were immediately sealed. Upon standing, themicrospheres were floating in a white top layer. The average particlesize was 3.6 microns with a concentration of 8.5×10⁸.

Table I gives the partial vapor pressures expected in the gas phaseusing this method to prepare microspheres with various hydrophobiccompounds at different bath temperatures.

                  TABLE I                                                         ______________________________________                                        Partial Vapor Pressures at Different Temperatures*                            ______________________________________                                        Perfluoropentane                                                                Bath Temperature 10° C. 20° C. 28° C.                    Vapor Pressure (atm)** 0.48 0.71 0.94                                         Perfluorohexane                                                               Bath Temperature 35° C. 45° C. 55° C.                    Vapor Pressure (atm)** 0.44 0.65 0.94                                         Perfluoroheptane                                                              Bath Temperature 59° C. 74° C. 79° C.                    Vapor Pressure (atm)*** 0.49 0.76 0.93                                        Perfluorooctane                                                               Bath Temperature 50° C. 65° C. 80° C.                    Vapor Pressure (atm)*** 0.20 0.36 0.55                                      ______________________________________                                         *Due to other factors, such as incomplete saturation of the gas phase wit     the hydrophobic compounds, a direct correlation cannot always be made         between the expected partial vapor pressures and the actual amount of         hydrophobic compound which becomes encapsulated.                              **Calculated by Antoine equation.                                             ***Estimated values from boiling pointpressure nomographs.               

EXAMPLE 3 In Vitro Ultrasonic Efficacy of Various MicrospherePreparations

The efficacy of microspheres for use as ultrasonic imaging agents can bepredicted based on their ability to demonstrate echogenicity at bodytemperature over a period of time. The following experiment was designedto test efficacy under conditions which would grossly approximate invivo conditions: Into a one liter plastic beaker containing 800 mL ofconstantly stirring saline solution saturated with air at 37° C., analiquot of a microsphere suspension was pipetted so that the finalconcentration was approximately 1×10⁴ microspheres per mL. Theechogenicity was tested with an HP Sonos 100 ultrasound machine and a 5MHz transducer. Testing was performed at a power setting of 30% undercontinuous or intermittent application of ultrasound. The images wererecorded on videotape and scored for image density relative to a set ofstandards at various time intervals.

Table II shows a comparison of various microsphere preparations made asdescribed in Example 1 with perfluoropropane gas saturated withdifferent hydrophobic compounds which were maintained at various bathtemperatures. Perfluoropropane-filled microspheres which were preparedwithout a hydrophobic compound are shown as the "control" microspheres.The gas flow rate was adjusted individually in order to take intoaccount the particle size intended. The mean particle sizes,concentrations and the longevity of their ultrasonic signal undercontinuous and intermittent ultrasonication (5 MHz transducer) aregiven. The intermittent sonication was carried out typically every 15minutes and had a duration of about 10 seconds while recording.

                  TABLE II                                                        ______________________________________                                        Properties of Perfluoropropane-filled Microspheres                              Hydrophobic                                                                              Mean   Concentration ×                                                                   Continuous                                                                            Intermittent                              Compound Size 10.sup.8 microspheres sonication Sonication                     (Bath temp.) (μm) per mL (min.) (min.)                                   ______________________________________                                        Control  3.6    22          10      60                                          C.sub.5 F.sub.12 (10° C.) 4.0 13 22 70                                 C.sub.5 F.sub.12 (20° C.) 3.8 16 17 80                                 C.sub.5 F.sub.12 (28° C.) 4.4 6.8 25 80                                C.sub.7 F.sub.16 (55° C.) 3.2 4.0 28 80                                C.sub.7 F.sub.16 (79° C.) 4.0 4.0 40 100                             ______________________________________                                    

As shown, all of the microsphere preparations which were prepared with ahydrophobic compound exhibited increased signal longevity.

EXAMPLE 4 In Vivo Diagnostic Imaging

Microspheres prepared as described in Example 1 are used in diagnosticimaging as follows: For a dog weighing approximately 25 kg, a 1.0 mLvolume of a microsphere suspension containing 5×10⁷ to 5×10⁹microspheres per mL are injected into a peripheral (cephalic) vein at arate of 0.3 mL per second. Images of the heart are acquired using aHewlett Packard Sonos 1500 (Andover, Mass.) ultrasonograph in the B-modeusing a transthoracic 5.0 mHz transducer. Images are recorded at a framerate of 30 frames per second throughout the procedure and stored onS-VHS tape for later processing.

What is claimed is:
 1. A composition for use as an ultrasonic imagingagent comprising an aqueous suspension of microspheres, saidmicrospheres comprising at least three phases:(a) a shell ofbiocompatible, amphiphilic material; (b) a liquid or solid hydrophobicbarrier formed by condensation of a hydrophobic compound at or belowroom temperature on the inner surface of said shell; and (c) a gaseousphase enclosed by said shell and said barrier.
 2. A composition of claim1, wherein the hydrophobic barrier is formed by condensation of ahydrophobic compound which is a linear or branced hydrocarbon of thegeneral formula C_(n) H_(2n+2), wherein n=6-12, or a linear or branchedperfluorocarbon of the general formula C_(n) F_(2n+2) wherein n=5-12, ora cyclic perfluorocarbon, or a perfluorinated alcohol or ether, or aalkyl trifluoroacetate or acyl chloride of the general formula C_(n)H_(2n+1) COCl wherein n=4-10, or a perfluorinated acyl chloride of thegeneral formula C_(n) F_(2n+1) COCl wherein n=4-10, or a polymerizablestyrene or alkyl acrylate of the general formula CH₂ ═CHCOOR, whereinR=C_(n) H_(2n+1), or C_(n) H_(2n+1), wherein n=1-6, and correspondingalkyl methacrylates and fluoroalkyl methacrylates.
 3. A composition ofclaim 2, wherein the hydrophobic compound is perfluoropentane.
 4. Acomposition of claim 2, wherein the hydrophobic compound is an alkylacrylate.
 5. A composition of claim 2, wherein the hydrophobic compoundis an alkyl methacrylate.
 6. A composition of claim 1, wherein the gasis insoluble.
 7. A composition of claim 1, wherein the gas is aperfluorocarbon gas.
 8. A composition of claim 1, wherein said barrieris a layer that covalently bonds to the inner surface of saidmicrosphere shell.
 9. A composition of 1, wherein said barrier is apolymerized layer that forms on the inner surface of said microsphereshell.